Medicament injection device

ABSTRACT

The present disclosure relates to medicament injection devices. An injection device includes: a movable dosage programming component comprising a rotary encoder system having a predefined angular periodicity, a sensor arrangement including a first optical sensor configured to detect movement of the movable dosage programming component relative to the sensor arrangement during dosing of a medicament, wherein the first optical sensor is configured to operate in a strobe-sampling mode at a first frequency, a second optical sensor configured to detect movement of the rotary encoder system relative to the second optical sensor wherein the second optical sensor is configured to operate in a strobe-sampling mode at a second frequency lower than the first frequency, and a processor arrangement configured to, based on the detected movement, determine a medicament dosage administered by the injection device.

CROSS REFERENCE TO RELATED APPLICATIONS

The present application is a continuation of U.S. patent applicationSer. No. 16/766,144, filed on May 21, 2020, which is the national stageentry of International Patent Application No. PCT/EP2018/082438, filedon Nov. 23, 2018, and claims priority to Application No. EP 17306626.7,filed on Nov. 23, 2017, the disclosures of which are incorporated hereinby reference.

TECHNICAL FIELD

The present disclosure is generally to medicament injection devices.

BACKGROUND

A variety of diseases exists that require regular treatment by injectionof a medicament. Such injection can be performed by using injectiondevices, which are applied either by medical personnel or by patientsthemselves. As an example, type-1 and type-2 diabetes can be treated bypatients themselves by injection of insulin doses, for example once orseveral times per day. For instance, a pre-filled disposable insulin pencan be used as an injection device. Alternatively, a re-usable pen maybe used. A re-usable pen allows replacement of an empty medicamentcartridge by a new one. Either pen may come with a set of one-wayneedles that are replaced before each use. The insulin dose to beinjected can then for instance be manually selected at the insulin penby turning a dosage knob and observing the actual dose from a dosewindow or display of the insulin pen. The dose is then injected byinserting the needle into a suited skin portion and pressing aninjection button of the insulin pen. To be able to monitor insulininjection, for instance to prevent false handling of the insulin pen orto keep track of the doses already applied, it is desirable to measureinformation related to a condition and/or use of the injection device,such as for instance information on the injected insulin dose.

SUMMARY

According to a first aspect, this disclosure describes an injectiondevice comprising: a movable dosage programming component comprising arotary encoder system having a predefined angular periodicity; a sensorarrangement comprising a first optical sensor configured to detectmovement of the movable dosage programming component relative to thesensor arrangement during dosing of a medicament, wherein the firstoptical sensor is configured to operate in a strobe-sampling mode at afirst frequency, and a second optical sensor configured to detectmovement of the rotary encoder system relative to the second opticalsensor, wherein the second optical sensor is configured to operate in astrobe-sampling mode at a second frequency lower than the firstfrequency; and a processor arrangement configured to, based on saiddetected movement, determine a medicament dosage administered by theinjection device.

The rotary encoder system may be configured to be rotatable with respectto the first optical sensor during a dialing mode of operation of theinjection device.

The rotary encoder system may comprise an encoder ring comprising aplurality of substantially light reflective flags arrangedcircumferentially around the encoder ring in accordance with thepredefined periodicity.

The encoder ring may comprise a plurality of substantially lightabsorbent flags arranged to alternate with the plurality ofsubstantially light reflective flags in accordance with the predefinedperiodicity.

Lateral edges of the plurality of substantially light reflective flagsmay be inwardly inclined.

The second optical sensor may be configured to operate in astrobe-sampling mode at a second frequency lower than the firstfrequency.

The first and second optical sensors may have an angular offset equal tohalf the predefined angular periodicity, with the first and secondoptical sensors configured to operate in a synchronous mode ofoperation.

The first and second optical sensors may have an angular offset thatdiffers from half the predefined angular periodicity, with the first andsecond optical sensors configured to operate in a staggered mode ofoperation with an offset time between sampling by the first and secondoptical sensors.

The angular offset may be less than half the predefined angularperiodicity.

The offset time may be varied based on a relative rotational speed ofrotary encoder system with respect to the first and second opticalsensors.

The offset time may be decreased in response to an increase in relativerotational speed.

The injection device may further comprise an injection button and anelectrical switch connected to the sensor arrangement, the electricalswitch arranged to supply power to the sensor arrangement in response toactuation of the injection button.

The injection device may further comprise a cartridge containing amedicament.

According to a second aspect, this disclosure describes a moduleconfigured to be used with or applied to an injection device comprisinga movable dosage programming component with a rotary encoder system,particularly an injection device as described herein, the modulecomprising: a sensor arrangement comprising at least one optical sensorbeing configured to detect movement of the movable dosage programmingcomponent of the injection device relative to the sensor arrangementduring dosing of a medicament and a collimating optics being arrangedbetween the at least one optical sensor and the movable dosageprogramming component; and a processor arrangement configured to, basedon said detected movement, determine a medicament dosage administered bythe injection device.

The collimating optics may comprise one or more of the following: one ormore discrete collimating lenses; one or more light pipes.

A discrete collimating lens may be arranged between each optical sensorand each light pipe and/or between each light pipe and the movabledosage programming component.

A single discrete collimating lens may be provided for each sensor andconfigured to cover the transmitter and/or receiver portion of thesensor.

The single discrete lens may be a lens array covering the sensor,particularly a micro-moulded lens array.

The one or more light pipes may have the shape of a frustum,particularly with a circular or an elliptic base,

According to a third aspect, this disclosure describes a method forprocessing signals generated by a sensor arrangement of an injectiondevice as described above and disclosed herein or a module as describedabove and disclosed herein, which comprises a sensor arrangement withtwo optical sensors arranged with a 180° shift such that the signal ofthe first sensor of the two sensors and the signal of the second sensorof the two sensors are in anti-phase, the method comprising the steps ofsetting a high threshold and a low threshold for the signal of the firstsensor and for the signal of the second sensor, respectively, andcounting a unit of a dose selected with the movable dosage programmingcomponent if the signal of the second sensor passes the high thresholdand thereafter passes the low threshold, and thereafter the signal ofthe first sensor passes the low threshold and thereafter passes the highthreshold.

The step of setting a high threshold and a low threshold for the signalof the first sensor and for the signal of the second sensor,respectively, may comprise a calibration step performed duringmanufacturing of the module for setting the high and low thresholds,wherein the calibration step comprises passing a set of calibrationgeometry beneath each sensor at controlled distances for calibration,and setting the high and low thresholds such that the high threshold isalways below the largest level of the respective sensor signal observedduring calibration and the low threshold is always below the smallestsignal level observed during calibration.

The step of setting a high threshold and a low threshold for the signalof the first sensor and for the signal of the second sensor,respectively, may comprise the steps of setting a sampling frequency forsampling the signals of both sensors to a level higher than a samplingfrequency used for normal operation and sampling the signals duringdelivery of a dose with an injection device comprising the module,determining the magnitudes of at least two consecutive peak-throughs ofthe signal of each sensor, and setting the high threshold and the lowthreshold for each signal to a percentage of the determined magnitudesof at least two consecutive peak-throughs if the determined magnitudesof at least two consecutive peak-throughs are within a predeterminedtolerance signal range.

According to a fourth aspect, this disclosure describes a method forprocessing signals generated by a sensor arrangement of an injectiondevice as described above and disclosed herein or a module as describedabove and disclosed herein, which comprises a sensor arrangement withtwo optical sensors arranged with a 180° shift such that the signal ofthe first sensor of the two sensors and the signal of the second sensorof the two sensors are in anti-phase, the method comprising the steps ofdetermining of a first crossover point when the level of the signal ofthe second sensor becomes greater than the level of the signal of thefirst sensor, determining of a second crossover point when the level ofthe signal of the first sensor becomes greater than the level of thesignal of the second sensor, and counting a unit of a dose selected upondetermining the first crossover point after having determined the secondcrossover point.

The determining of a crossover point when the level of the signal of theone sensor becomes greater than the level of the signal of the othersensor may comprise determining that the difference of the levels of thesignals of both sensors exceeds a predetermined threshold.

The method may further comprise a calibration step performed duringmanufacturing of the module for matching the signals of both sensors interms of mean signal and signal amplitude, wherein for calibration a setof calibration geometry is passed beneath each sensor at controlleddistance and scaling factors for mean and amplitude are applied to thesecond sensor to match the mean and amplitude of its signal to the meanand amplitude of the signal of the first sensor. Alternatively, themethod may further comprise a calibration step performed after selectinga dose, wherein for calibration a dataset for the signals of bothsensors is stored and scaling factors are retrospectively calculatedfrom the stored dataset in order to obtain a common mean and amplitudebetween the signals of both sensors.

According to a fifth aspect, this disclosure describes a method forprocessing signals generated by a sensor arrangement of an injectiondevice as described above and disclosed herein or a module as describedabove and disclosed herein, which comprises a sensor arrangement withtwo optical sensors arranged with a 180° shift such that the signal ofthe first sensor of the two sensors and the signal of the second sensorof the two sensors are in anti-phase, the method comprising the steps ofdetermining peaks of the signals of the first sensor and the secondsensor during selection of a dose, and counting a unit of a doseselected when a peak of the signal of the first sensor has been detectedafter a peak of the signal of the second sensor has been detected.

According to a sixth aspect, this disclosure describes an injectiondevice comprising: a rotary encoder system having a predefined angularperiodicity and an encoder ring comprising a plurality of lightreflectors arranged circumferentially around the encoder ring inaccordance with the predefined periodicity, wherein each light reflectoris designed for total internal reflection of an incident light beam; asensor arrangement comprising a light emitter arranged to emit a lightbeam directed to a light reflector of the encoder ring and two lightreceivers arranged to receive a light beam reflected by the lightreflector of the encoder ring, wherein the sensor arrangement isconfigured to detect movement of the movable dosage programmingcomponent relative to the sensor arrangement during dosing of amedicament; and a processor arrangement configured to, based on saiddetected movement, determine a medicament dosage administered by theinjection device.

Each light reflector may comprise two reflecting surfaces arrangedperpendicular to each other such that an incident light beam isreflected from one reflecting surface to the other reflective surfaceand reflected from the other reflective surface to the light receivers.

The light reflectors may be made from a transparent material and the tworeflecting surfaces of each light reflector are high-polished in orderto reflect light incident on the light reflector.

Either the rotary encoder system or the sensor arrangement may beconfigured to be rotated during dosing of a medicament.

BRIEF DESCRIPTION OF THE FIGURES

So that the general concepts set out in the foregoing sections can bemore fully understood, embodiments thereof will be described withreference to the accompanying drawings, in which:

FIG. 1 shows an injection device according to a first embodiment;

FIG. 2 shows a proximal end of an injection device according to a secondembodiment;

FIG. 3A shows a proximal end of the injection device of FIG. 2 afteractuation of an injection button;

FIG. 3B is a cross-sectional view of the injection device of FIG. 2after actuation of the injection button;

FIG. 4 is a zoomed-in cross-sectional view of the injection device ofFIG. 2 ;

FIG. 5 is an elevated side view of a first type of encoder system;

FIG. 6 is a plan view of the encoder system shown in FIG. 5 ;

FIG. 7 is a schematic block diagram of a device controller;

FIG. 8A is a cross-sectional view of the proximal end of a device beforeactuation of an injection button;

FIG. 8B is a cross-sectional view of the proximal end of a device duringpartial actuation of an injection button;

FIG. 8C is a cross-sectional view of the proximal end of a device duringfull actuation of an injection button;

FIG. 9 is an elevated side view of a second type of encoder system;

FIG. 10 is a plan view of the encoder system shown in FIG. 9 ;

FIG. 11 illustrates a Gray code output;

FIG. 12 is a partial plan view of an encoder system;

FIG. 13 is a partial plan view of an encoder system;

FIG. 14 is an elevated side view of a third type of encoder system;

FIG. 15A is a partial plan view of an encoder system;

FIG. 15B is a partial plan view of an encoder system;

FIG. 16 is an elevated side view of a fourth type of encoder system;

FIG. 17 is an elevated side view of a fifth type of encoder system;

FIG. 18A is a plan view of a sixth type of encoder system;

FIG. 18B is a plan view of a seventh type of encoder system;

FIG. 19A is a screenshot showing scope traces obtained from variousembodiments;

FIG. 19B is a close-up view of the screenshot of FIG. 19A;

FIG. 20A shows a first method for varying the strobe of an LED of thesensors;

FIG. 20B shows a second method for varying the strobe of an LED of thesensors;

FIG. 20C shows a third method for varying the strobe of an LED of thesensors;

FIG. 21 is an elevated side view of an eight type of encoder system;

FIG. 22 is a plan view of the encoder system shown in FIG. 19 ;

FIG. 23 is a schematic for demonstrating the light guidance with a lightpipe of a sensor arrangement used in the eight type encoder system ofFIGS. 20 and 21 ;

FIG. 24 is a schematic for demonstrating the light guidance with a lightpipe and collimating lenses of a sensor arrangement used in the eighttype encoder system of FIGS. 20 and 21 ;

FIG. 25 is an elevated side view of an electronic module sub assemblycomprising a separate injection moulded component with a light guidance;

FIG. 26 is an elevated side view of the separate injection mouldedcomponent comprising collimating lenses of the light guidance;

FIG. 27 is an elevated side view of another electronic module subassembly comprising an integrally injection moulded collimating lensesassembly of a light guidance with a tool side-action to form distalsurfaces of the collimating lenses;

FIG. 28 is a side view of the electronic module sub assembly of FIG. 27showing the formed distal surfaces of the collimating lenses;

FIG. 29 shows four schematics of four alternative collimating lensassemblies for implementing a light guidance for the eight type ofencoder system;

FIG. 30 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement during movement of a movable dosageprogramming component relative to the sensor arrangement according to anembodiment;

FIG. 31 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement during movement of a movable dosageprogramming component relative to the sensor arrangement and the settingof a “high” and “low” static threshold voltage for the signal voltagesof each optical sensor of a sensor arrangement according to anembodiment of a first algorithm;

FIG. 32 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement during movement of a movable dosageprogramming component relative to the sensor arrangement and the settingof a “high” and “low” dynamic threshold voltage for the signal voltagesof each optical sensor of a sensor arrangement according to anembodiment of a second algorithm;

FIG. 33 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement that are typically not matched in termsof mean voltage and voltage amplitude;

FIG. 34 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement during movement of a movable dosageprogramming component relative to the sensor arrangement and thedetecting of a crossover point of the signal voltages of each opticalsensor of a sensor arrangement according to an embodiment of a thirdalgorithm;

FIG. 35 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement during movement of a movable dosageprogramming component relative to the sensor arrangement and thedetecting of a low power peak of the signal voltages of each opticalsensor of a sensor arrangement according to an embodiment of a fifthalgorithm;

FIG. 36 shows a partial cross-sectional side view of a proximal end ofan injection device according to a third embodiment; and

FIG. 37 shows the course of signal voltages generated by two opticalsensors of a sensor arrangement during movement of a movable dosageprogramming component relative to the sensor arrangement according tothe third embodiment of the injection device.

DETAILED DESCRIPTION

In the following, embodiments will be described with reference to aninsulin injection device. The present disclosure is however not limitedto such application and may equally well be deployed with injectiondevices that eject other medicaments.

Embodiments are provided in relation to injection devices, in particularto variable dose injection devices, which record and/or track data ondoses delivered thereby. These data may include the size of the selecteddose, the time and date of administration, the duration of theadministration and the like. Features described herein include thearrangement of sensing elements, power management techniques (tofacilitate small batteries) and a trigger switch arrangement to enableefficient power usage.

Certain embodiments in this document are illustrated with respect toSanofi's AllSTAR® injection device where an injection button and gripare combined. The mechanical construction of the AllSTAR® injectiondevice is described in detail in the international patent applicationWO2014/033195A1, which is incorporated herein by reference. Otherinjection devices with the same kinematical behaviour of the dialextension and trigger button during dose setting and dose expellingoperational mode are known as, for example, the Kwikpen® device marketedby Eli Lilly and the Novopen® device marketed by Novo Nordisk. Anapplication of the general principles to these devices therefore appearsstraightforward and further explanations will be omitted. However, thegeneral principles of the present disclosure are not limited to thatkinematical behaviour. Certain other embodiments may be conceived forapplication to Sanofi's SoloSTAR® injection device where there areseparate injection button and grip components.

In the following discussion, the terms “distal”, “distally” and “distalend” refer to the end of an injection device towards which a needle isprovided. The terms “proximal”, “proximally” and “proximal end” refer tothe opposite end of the injection device towards which an injectionbutton or dosage knob is provided.

FIG. 1 is an exploded view of a medicament delivery device. In thisexample, the medicament delivery device is an injection device 1, suchas Sanofi's AllSTAR® injection pen.

The injection device 1 of FIG. 1 is a pre-filled, disposable injectionpen that comprises a housing 10 and contains an insulin container 14, towhich a needle 15 can be affixed. The needle is protected by an innerneedle cap 16 and either an outer needle cap 17 other cap 18. An insulindose to be ejected from injection device 1 can be programmed, or ‘dialedin’ by turning a dosage knob 12, and a currently programmed dose is thendisplayed via dosage window 13, for instance in multiples of units. Forexample, where the injection device 1 is configured to administer humaninsulin, the dosage may be displayed in so-called International Units(IU), wherein one IU is the biological equivalent of about 45.5micrograms of pure crystalline insulin (1/22 mg). Other units may beemployed in injection devices for delivering analogue insulin or othermedicaments. It should be noted that the selected dose may equally wellbe displayed differently than as shown in the dosage window 13 in FIG. 1.

The dosage window 13 may be in the form of an aperture in the housing10, which permits a user to view a limited portion of a dial sleeve 70that is configured to move when the dosage knob 12 is turned, to providea visual indication of a currently programmed dose. The dosage knob 12is rotated on a helical path with respect to the housing 10 when turnedduring programming.

In this example, the dosage knob 12 includes one or more formations 71a, 71 b, 71 c to facilitate attachment of a data collection device.

The injection device 1 may be configured so that turning the dosage knob12 causes a mechanical click sound to provide acoustical feedback to auser. The dial sleeve 70 mechanically interacts with a piston in insulincontainer 14. In this embodiment, the dosage knob 12 also acts as aninjection button. When needle 15 is stuck into a skin portion of apatient, and then dosage knob 12 is pushed in an axial direction, theinsulin dose displayed in display window 13 will be ejected frominjection device 1. When the needle 15 of injection device 1 remains fora certain time in the skin portion after the dosage knob 12 is pushed, ahigh percentage of the dose is actually injected into the patient'sbody. Ejection of the insulin dose may also cause a mechanical clicksound, which is however different from the sounds produced when rotatingthe dosage knob 12 during dialing of the dose.

In this embodiment, during delivery of the insulin dose, the dosage knob12 is returned to its initial position in an axial movement, withoutrotation, while the dial sleeve 70 is rotated to return to its initialposition, e.g. to display a dose of zero units.

Injection device 1 may be used for several injection processes untileither the insulin container 14 is empty or the expiration date of themedicament in the injection device 1 (e.g. 28 days after the first use)is reached.

Furthermore, before using injection device 1 for the first time, it maybe necessary to perform a so-called “prime shot” to remove air frominsulin container 14 and needle 15, for instance by selecting two unitsof insulin and pressing dosage knob 12 while holding injection device 1with the needle 15 upwards. For simplicity of presentation, in thefollowing, it will be assumed that the ejected amounts substantiallycorrespond to the injected doses, so that, for instance the amount ofmedicament ejected from the injection device 1 is equal to the dosereceived by the user. Nevertheless, differences (e.g. losses) betweenthe ejected amounts and the injected doses may need to be taken intoaccount.

As explained above, the dosage knob 12 also functions as an injectionbutton so that the same component is used for dialing and dispensing.

FIGS. 2, 3A and 3B show the proximal end of a device 2 according to asecond embodiment. The device 2 comprises a grip 205 and injectionbutton 210. Unlike the device 1 shown in FIG. 1 , the injection button210 is separate from the grip 205 which is used to dial the dosage. Thedial sleeve 70 and injection button 210 are located partially inside thegrip 205. The grip 205 and dial sleeve 70 may be considered functionallyas elements of the same component. Indeed, the grip 205 and dial sleeve70 may only be separate components for assembly reasons. Aside from thedifferences described herein, the device 2 shown in FIG. 2 operates insubstantially the same way as the device 1 shown in FIG. 1 .

Similarly to the device 1, the dial sleeve 70, grip 205 and injectionbutton 210 extend helically from the device 2. During a dose-dialingmode of operation (as shown in FIG. 2 ) there is no relative rotationbetween the injection button 210 and the dial sleeve 70. The dose isdialed by rotating the grip 205 (thereby also rotating the dial sleeve70 and injection button 210) with respect to the rest of the device 2.

To initiate dispensing of a medicament, the injection button 210 ispressed axially, as shown in FIGS. 3A and 3B. This action changes themode of the device 2 to a dispensing mode. In dispensing mode the dialsleeve 70 and grip component 205 retract along a helical path into therest of the device 2, whereas the injection button 210 does not rotateand only retracts with axial motion. Thereby, in dispensing mode, thereis a disengagement of the injection button 210 leading to relativerotation of the injection button 210 with respect to the dial sleeve 70.This disengagement of the injection button 210 with respect to the dialsleeve 70 is caused by a clutch arrangement described in more detail inrelation to FIGS. 8A-C.

FIG. 4 is a close-up cross sectional view of the proximal end of thedevice 2 shown in FIG. 3 after the injection button 210 has beenpressed. As shown in FIG. 4 , the injection button 210 is configured astwo separate sub-components, namely a distal or lower button part 210 aand a proximal or upper button part 210 b. The injection button 210 maybe configured in this way to aid the assembly process. The distal buttonpart 210 a and proximal button part 210 b may be fixed together and actfunctionally as a single component, i.e. the injection button 210.

A sensor arrangement 215 comprising one or more optical sensors ismounted in the injection button 210 which is configured to sense therelative rotational position of the dial sleeve 70 relative to theinjection button 210. This relative rotation can be equated to the sizeof the dose dispensed and used for the purpose of generating and storingor displaying dose history information. The sensor arrangement 215 maycomprise a primary (optical) sensor 215 a and a secondary (optical)sensor 215 b. In FIG. 4 , only the secondary sensor 215 b is shown.

FIGS. 5 and 6 show an encoder system 500 according to certainembodiments. The encoder system is configured for use with the device 2described above. As shown in FIG. 5 and FIG. 6 , the primary sensor 215a and secondary sensor 215 b are configured to target specially adaptedregions at the proximal end of the dial sleeve 70. In this embodiment,the primary sensor 215 a and secondary sensor 215 b are infrared (IR)reflective sensors. Therefore, the specially adapted proximal regions ofthe dial sleeve 70 are divided into a reflective area 70 a and anon-reflective (or absorbent) area 70 b. The part of the dial sleeve 70comprising the reflective area 70 a and a non-reflective (or absorbent)area 70 b may be termed an encoder ring.

To keep production costs to a minimum, it may be favourable to formthese areas 70 a, 70 b from injection moulded polymer. In the case ofpolymer materials, the absorbency and reflectivity could be controlledwith additives, for example carbon black for absorbency and titaniumoxide for reflectivity. Alternative implementations are possible wherebythe absorbent regions are moulded polymer material and the reflectiveregions are made from metal (either an additional metal component, orselective metallisation of segments of the polymer dial sleeve 70).

Having two sensors facilitates a power management technique describedbelow. The primary sensor 215 a is arranged to target a series ofalternating reflective regions 70 a and non-reflective regions 70 b at afrequency commensurate with the resolution required for the dose historyrequirements applicable to a particular drug or dosing regimen, forexample, 1 IU. The secondary sensor 215 b is arranged to target a seriesof alternating reflective regions 70 a and non-reflective regions 70 bat a reduced frequency compared to the primary sensor 215 a. It shouldbe understood that the encoder system 500 could function with only aprimary sensor 215 a to measure the dispensed dose. The secondary sensor215 b facilitates the power management technique described below.

The two sets of encoded regions 70 a, 70 b are shown in FIGS. 5 and 6concentrically with one external and the other internal. However, anysuitable arrangement of the two encoded regions 70 a, 70 b is possible.Whilst the regions 70 a, 70 b are shown as castellated regions, itshould be borne in mind that other shapes and configurations arepossible.

The devices 1, 2 also include a controller 700, as shown schematicallyin FIG. 7 . The controller 700 comprises a processor arrangement 23including one or more processors, such as a microprocessor, a DigitalSignal Processor (DSP), Application Specific Integrated Circuit (ASIC),Field Programmable Gate Array (FPGA) or the like, together with memoryunits 24, 25, including program memory 24 and main memory 25, which canstore software for execution by the processor arrangement 23.

The controller 700 controls a sensor arrangement 215, comprising one ormore sensors 215 a, 215 b, is provided.

An output 27 is provided, which may be a wireless communicationsinterface for communicating with another device via a wireless networksuch as Wi-Fi or Bluetooth®, or an interface for a wired communicationslink, such as a socket for receiving a Universal Series Bus (USB),miniUSB or micro-USB connector. For example, data may be output to adata collection device attached to the device 1, 2.

A power switch 28 is also provided, together with a battery 29.

Power Management

It is advantageous to be able to minimise the power usage of the encodersystem 500 so that the size of a battery 29 needed to be packaged intothe device 1, 2 can be minimised. The sensors 215 a, 215 b used in thisembodiment require a certain amount of power to operate. This embodimentis arranged such that the sensors 215 a, 215 b can be switched on andoff intermittently at a controlled frequency (i.e. in a strobe-samplingmode). There is inherently a limit to the maximum rotational speed thatcan be counted by a sampled encoder system before aliasing occurs.Aliasing is the phenomenon where the sampling rate is less than the rateat which sensed regions pass the sensor which means that a miscountcould occur when a region change is missed. The secondary sensor 215 bwith a reduced frequency compared to the primary frequency 215 a cantolerate a higher rotational speed before it too becomes aliased. Whilstthe secondary sensor 215 b is not able to resolve the dose dispensed tothe same resolution as the primary sensor 215 a, the output of thesecondary sensor 215 b remains reliable at higher speeds. Therefore bothsensors 215 a, 215 b are used in combination to be able to accuratelydetermine dose delivered up to a first threshold rotational (dispensing)speed. The sensors 215 a, 215 b can then be used to determine anapproximate dose delivered up to a second (higher) threshold dosingspeed. At speeds above the second threshold speed the sensors 215 a, 215b will not be able to accurately or approximately determine the dosedelivered, therefore the second threshold is set above a speed which isnot physically possible in the injection device 1, 2.

The first speed threshold is determined by the sampling rate of primarysensor 215 a and the frequency of encoder region transitions, which isfixed at the resolution required by the intended drug or dosing regimen(for example one transition per 1 IU). The second speed threshold isdetermined by the sampling rate of the secondary sensor 215 b and thefrequency of encoder region transitions. The first threshold is set suchthat the largest range of dispensing speeds can be covered by the systemfor accurate reporting of dose dispensed.

The example embodiment shown in FIG. 6 has primary sensor 215 atargeting region transitions at 1 transition per 1 IU of dose deliveredand the secondary sensor 215 b targeting region transitions at 1transition per 6 IU of dose delivered. Other options are possible whichinclude 1 transition per 2 IU, 1 transition per 4 IU, 1 transition per 8IU and 1 transition per IU units. These options are each possiblebecause there are 24 separate regions 70 a, 70 b per revolution in theencoder system 500 shown in FIG. 6 . In general, if the number ofseparate regions 70 a, 70 b per revolution were n units then there wouldbe options at one region transition per m units where m was any integerfactor of n greater than 1 and less than n.

The slower the sampling frequency of both sensors 215 a, 215 b, thelower the power consumption required and therefore the smaller therequired size of the battery 29. It is therefore optimal to minimise, bydesign, the sampling frequency as far as is practical.

Trigger Switch Arrangement

In order to further limit the battery capacity requirement, it isadvantageous to be able to have the device 2 in a low power state whenthe sensors 215 a, 215 b are not required to be energised. This isachieved with a switch activated by the displacement of the injectionbutton 210.

As shown in FIG. 8A, a switch 800 is mounted in the injection button210. In the configuration shown in FIG. 8A, an arm of the switch 800 isdeflected by the dial sleeve 70 so that the switch 800 is in an openstate. In this configuration a clutch between a clutch component and thedial sleeve 70 is engaged with the device 2 in its dialing mode. As theinjection button 210 is pressed the injection button 210 is displacedaxially with respect to the dial sleeve 70, therefore the switch 800 isdisplaced axially relative to the dial sleeve 70. This displacementcauses a part on the dial sleeve 70 to ride down a cam surface on theswitch 800, allowing the switch arm to deflect towards its free state.This deflection in the switch arm has the effect of changing theelectrical state of the switch 800 (for example to electrically closed).The design is arranged such that the electrical change of state of theswitch 800 happens before the state change in the clutch between theclutch component and dial sleeve 70. FIG. 8B shows the transition pointof the clutch and shows that the switch 800 has already changed state.FIG. 8C shows the state of the device 2 with the injection button 210fully pressed. In this condition, the clutch is fully separated allowingthe clutch component and dial sleeve 70 to rotate relative to each otherin the dispense mode.

This sequence operates in reverse when the injection button 210 isreleased.

The change in electrical state that occurs when the injection button 210is pressed thereby allowing the device 2 to be powered down into a lowenergy consumption state when the injection button 210 is not pressed.Relative rotation between the injection button 210 and dial sleeve 70 isnot possible, therefore the encoder system 500 is not required in thisstate.

It is possible for the mechanical configuration between the dial sleeve70 and the switch 800 to operate in the opposite sense such that the armof the switch 800 is deflected during dispensing rather than duringdialing.

The following embodiments relate to an alternative sensing technique todetermine the number of medicament units that have been dispensed fromthe device 1, 2.

As with the embodiments described above, two sensors 215 are mounted inthe injection button 210 and are configured to sense the relativerotational position of the dial sleeve 70 relative to the injectionbutton 210 during the dispensing of a dose. This relative rotation canbe equated to the size of the dose dispensed and used for the purpose ofgenerating and storing or displaying dose history information.

As shown in FIG. 9 , the two sensors 215 from this embodiment areconfigured to target specially adapted regions 70 a, 70 b of the dialsleeve 70. In this embodiment IR reflective sensors are used, thereforethe regions of the dial sleeve 70 are divided into reflective andabsorbent segments 70 a, 70 b. The segments 70 a, 70 b may also bereferred to herein as flags.

Unlike the encoder system 500 described above in relation to FIGS. 5 and6 , the encoder system 900 shown in FIGS. 9 and 10 has both IR sensors215 target the same type of region 70 a, 70 b. In other words, thesensors 215 are arranged so that they both face reflective regions 70 aor both face absorbent regions 70 b at the same time. During thedispensing of a dose, the dial sleeve 70 rotates anti-clockwise 15°relative to the injection button 210 for every medicament unit that hasbeen dispensed. The alternate flag elements are in 30° (or two unit)sections. The sensors 215 are arranged to be out of phase with eachother, such that the angle between them equates to an odd number ofunits (e.g. 15°, 45°, 75°, etc.), as shown in FIG. 10 .

The encoder system 900 shown in FIG. 10 has 12 units per revolution,i.e. 12 alternating regions 70 a, 70 b. In general, embodiments workwith any multiple of 4 units per revolution. The angle, α, betweensensors 215 can be expressed by Equation 1, where both m and n are anyintegers and there are 4 m units dispensed per revolution.

$\begin{matrix}{\sigma = {\left( {{2n} - 1} \right)\frac{360}{4m}}} & {{{Equation}1}‐{{Angle}{between}{sensors}}}\end{matrix}$

FIG. 11 shows how the outputs for a Sensor A and Sensor B change as thedial sleeve 70 rotates anti-clockwise during dispensing of a medicament.

In combination, the two sensors A, B produce a 2-bit Gray code output(11, 01, 00, 10). The 2-bit code sequence repeats every four unitsdispensed. This coded output facilitates the detection of positive(anticlockwise) and negative (clockwise) rotations. For example, whenthe sensors read ‘11’ a change to ‘01’ would be a positive rotation andthe change to ‘10’ would be a negative rotation. This directionallysensitive system has advantages over a purely incremental system, in theability to accurately determine true dispensed dose volume in the caseswhere negative rotations can occur. For example, in mechanisms that overrotate at the end of dose stop before ‘backing-off’ when the userreleases the injection button 210.

Referring to FIG. 12 , the IR sensors 215 emit IR light from an LED. TheIR reflective regions 70 a of the encoder system 900 reflect the lightand the sensors detect the reflected light. The sensors 215 then convertthe detected light to an electrical output. The strength of the IR lightthat is detected by the sensor 215 after reflecting off the encoder ringis proportional to the proximity of the sensor to the encoder ring.Therefore it is desirable for the sensor 215 to be as radially close tothe encoder ring as possible without contacting the encoder ring, whichwould add frictional losses to the dispense mechanism.

Referring to FIG. 13 , the IR absorbent regions 70 b of the dial sleeve70 do not completely absorb all the IR light emitted from the sensor215. Testing shows that when the sensor 215 is aligned with theabsorbent regions 70 b of the dial sleeve 70 the sensors 215 have someelectrical output due to the low level of IR light reflected by the dialsleeve 70. Therefore, the dial sleeve flags have been designed tomaximise the distance between the sensor 215 and any reflective parts ofthe encoder ring. This ensures a high contrast ratio and signalsharpness.

As a dose is dispensed, the software of the device 1, 2 monitors theelectrical output of the sensors 215. The software detects changesbetween high and low outputs to determine when the relative rotationbetween the dial sleeve 70 and injection button 210 has reached anadditional 15° (i.e. an additional one unit has been dispensed).Therefore it is beneficial to the function of the device for thecontrast ratio between the high and low outputs to be as large aspossible.

According to various embodiments, the design of the dial sleeve 70 andencoder ring flags 70 a, 70 b has been developed to increase thecontrast ratio. The design shown in FIG. 14 has the absorbent dialsleeve flags 70 b removed to leave gaps 140 between adjacent encoderring flags 70 a. This maximises the distance between the sensor 215 andany material which could reflect any of the IR light emitted from thesensor.

This design increases the contrast ratio between the low and high sensorelectrical outputs. However, as FIG. 15A shows, the IR light emitted bythe sensor 215 is not a beam, such that as the dial sleeve 70 rotatesbetween a reflective encoder ring flag 70 a and a gap 140, there isoverlap where the sensor 215 detects some of the light emitted by thesensor 215. During this period, the sensor output gradually decreasesfrom high to low, rather than an immediate step change between high andlow. This gradual decrease is more difficult for the software todetermine as a 15° rotation (i.e. one medicament unit dispensed), thanan immediate step change.

This phenomenon occurs with various embodiments of the encoder flags (asshown in FIG. 9 and FIG. 14 ). However, as shown in FIG. 15B, inaccordance with certain embodiments, the rotation of the dial sleeve 70that is required before the sensor output completely switches to a lowoutput is increased due to the visibility of the sides of the reflectiveencoder ring flags 70 a.

Therefore, it is advantageous to reduce the thickness at the edges ofthe IR reflective flags 70 a on the encoder ring. FIG. 16 and FIG. 17show two possible embodiments to reduce the thickness at the lateraledges of the IR reflective flags 70 a on the encoder ring so that thereflective surfaces are inclined inwardly for preventing or reducingscattered reflection, thereby enhancing contrast transition and signalsharpness.

FIG. 16 shows an embodiment where the moulded polymer encoder ring hasbeen replaced with a formed metal ring 160.

FIG. 17 shows an embodiment where the moulded polymer encoder ring hasbeen replaced by sections of the dial sleeve 70 that have been printed,painted or coated with IR reflective material.

FIGS. 18A and 18B illustrate two alternative modes of operation inaccordance with various embodiments. Referring to FIG. 18A, Sensor I andSensor II are provided having an angular offset (δ) is half of theperiodicity (ϕ) of the encoded regions of the encoder ring. In thisembodiment, the sensors are operated to sample synchronously, i.e. atthe same times (t₁, t₂, t₃, . . . ). FIG. 18A illustrates an embodimentwhere the angular offset (δ) differs from half of the featureperiodicity (ϕ/2) and the sensors are operated in a staggered mode withan offset in time (Δt) between samplings. This may be used to achievemore balanced overall system LED power consumption than available insynchronous operation.

In the configuration shown in FIG. 18B, the amount of the angular offset(δ) may be decreased below half of the feature periodicity (ϕ) in orderto compensate for the relative angular travel during the offset in time(Δt) between the sampling operations of the different sensors.

The offset in time (Δt) may be adjusted according to an estimated valuefor the relative rotational speed (ω) of the encoder ring which may becalculated from the sensor measurements. In particular, the offset time(Δt) may be decreased when an increase in rotational speed (ω) isdetermined.

FIG. 19A shows scope traces obtained by embodiments of the disclosure.The lower trace is the LED driving signal and the upper trace is theoutput from the current mirror before the Schmitt trigger.

FIG. 19B is a zoomed-in view of the scope traces shown in FIG. 19A.Results show that it is possible to sample at 256 μs with a nearly12-to-1 duty cycle (meaning the average current is 1/12^(th) of the 4 mALED drive, thereby saving power and cell capacity. This is equivalent toa sample rate of over 3900 Hz and with one unit per segment and aminimum of two samples per segment a detection speed in excess of 1950units per second is achieved without violating the Nyquist criterion. Assuch, no anti-aliasing detector is required.

FIGS. 20A, B and C shows an embodiment of a method for varying thestrobe of an LED of the sensors with the currently detected angularvelocity. The highest trace in FIGS. 20A, B and C represent the LEDstrobe, the lowest trace the acceleration of the sensors. The middletraces represent the signals generated by the sensors.

The strobe frequency of the LED may be kept at a low value as long asthere is no change at the optical sensors and it can be assumed that thedrive is at a standstill (angular velocity is zero).

With the first change of state at a sensor (the angular velocity isincreased), the scanning frequency may be increased in order to detectthe beginning rotation with sufficient accuracy. Furthermore, thefrequency can be increased with increasing angular velocity in themanner of a tracking system, as shown in the lowest trace. Inparticular, this tracking can be set up in such a way that a loss in theresolution of the light barrier is sufficiently counteracted.Furthermore, the resolution at a detected angular velocity canparticularly be set so high that even with the maximum acceleration ofthe drive to be considered, a sufficiently fast readjustment of thescanning frequency is possible.

Due to the acceleration, the signals of the sensors are not quite 90°symmetrical (as shown by the two middle traces in FIGS. 20A, B and C).As soon as the sensor rotates at a constant angular speed, the signalsare exactly 90° offset.

In FIGS. 20A, B and C, it can be seen how with increasing angularvelocity the illumination created by the LED strobe receives an everhigher scanning frequency in order to adjust the density, or dutyfactor, of the strobing along the time for always providing sufficientresolution in view of the actual motion state of the rotor.

The four timelines provided in each of FIGS. 20A, B and C may helpillustrating some exemplary embodiments for a method of an adaptiveadjustment of the strobe frequency in accordance to the detectedmomentary angular velocity for achieving a trading-of between powersaving and reliability in detection.

Here, for the sake of simplification it shall be assumed that theencoder illumination strobe is synchronous in the meaning of assumingboth detectors being powered to produce light flashes of essentially thesame length at essentially the same points in time. These strobe flashesare illustrated by the white gaps in the uppermost timeline denoted “LEDStrobe”. The black regions in between can be understood as the timeintervals without any illumination on either sensor. Apparently, themean power required for the sensor illumination corresponds to thenumber of strobes per time unit because of the constant strobe duration.In the exemplary situation of the exemplary strobe timeline in FIG. 20A,the increase in time density of the strobes from left to right thereforetranslates into a proportional increase in illumination powerconsumption. This increase, however, allows the sensors to correctlydetermine the operational state and velocity of the encoder rotor duringphases of acceleration as will be explained subsequently.

In order to facilitate the understanding of the rotational kinematics ofthe mechanism coupled to the encoder rotor, the momentary angularvelocity of the encoder rotor is provided in the lowermost timeline ineach of FIGS. 20A, B and C, denoted by “Angular Velocity”. Again, forthe sake of simplification in all three situations an acceleration modelwith piecewise linear behaviour has been chosen. In particular, it shallbe assumed that the mechanism undergoes, after a short initial time atrest, a linear increase in angular speed, in the way of a constantacceleration and, after a more elongated time interval denoted“Acceleration”, reaches a maximum rotational speed for the final time inconsideration. This can be understood as a first order approximation tothe dynamics of the mechanism under the assumption of a constant forcebeing applied by the user for actuation. Due to the linear response ofthe conversion mechanism, a constant force will translate into aconstant torque that can serve for acting against frictional effects inthe baseline and for accelerating the mechanism. Additionally, asanother simplification, it is assumed that the rotational speed will notincrease beyond a maximum value whereat the overall frictional lossequals to the input torque. This is to reflect the fluid frictioncharacteristic of the liquid expelling which, in a first approximation,monotonically increases with the flow rate of expelling. In thesimplified model, the equilibrium is approached on a linear ramp asshown in the lowermost graph even though a more realistic modellingmight rely on an asymptotic approaching to the maximum rotational speed.This, however, would not introduce a qualitative difference in view ofthe adaptive strobe sensor operation which shall be explained here.

Even though strobing based sensor operation has may yield someadvantages in view of power consumption it suffers some systematiclimitation when it comes to higher rotational speed or higher angularvelocity. This can be understood more easily when looking at the secondand third timelines where the continuous sensor intensity pattern infront of the respective optical sensor is illustrated. Here, “continuousintensity pattern” shall be understood as the intensity pattern therespective optical detector would detect under a fully continuousillumination without any gaps or interruptions over time. The effectivedetector reading, however, results from applying an “AND” operation tothe value in the “LED Strobe” timeline and the respective “continuousintensity pattern” of the respective sensor. In a direct clue it can bederived, that in a situation wherein the strobes pulses match witheither the darker or lighter areas in the “continuous intensity pattern”for a respective sensor in fixed phase relation, no change in the sensorreading will be observed and the signals might erroneously beinterpreted by the processor towards a stationary angular position ofthe rotor. This may be considered as a worst case scenario wherein novalid information can be derived from the sensor signals at all in viewof the rotational state. Apparently, there are other scenarios whereinonly some information is lost in view of rotational transitions in oneor another sensor. This can be imagined similar to a Moiré effectproduced by the overlay of the strobe pulses and the moving brightnesspatterns.

Keeping this in mind, the timelines in FIGS. 20A, B and C may provide anexample on how a generally more adequate scheme of increasing the strobedensity along the time in response to a change in the rotational stateof the rotor can help avoiding or at least reducing wrong sensorreadings. A closer look to the “AND” between the first timeline and thesecond respective third timeline on the other hand indicates that alimited anticipatory increase in strobe density over time may alreadysufficiently address the issue when the mechanisms rotationalacceleration can be assumed remaining below a known threshold valueand/or when the maximum in angular velocity of the rotor can be assumedto remain below a known threshold value. As explained before theseassumptions are fulfilled in a typical injection pen use case scenariowherein the accelerating torque is derived by mechanical conversion ofthe linear force a user applies to an actuation member, e.g. the dialextension.

In view of this, a rather simple and easy to implement scheme for theadaption of the strobe density over time can be seen in a digitalswitching between a first, lower density value and a second, higherdensity value. Variants thereof are illustrated in FIGS. 20B/C. Both aredesigned for switching from the first value to the second value would beperformed upon detection of the earliest transition from the stationaryto the non-stationary situation and for switching back upon detection ofa stationary state for a pre-determined amount of time. Clearly, thedetermination of whether a stationary state or a non-stationary state isreached has to be made on the basis of the sensor readings and some carehas to be applied to avoid artefacts as explained before.

Specific variants on this general switching approach are illustrated inFIGS. 20B and 20C, respective. In particular, FIG. 20B provides anexemplary timeline for a “LED Strobe” density which is, directly after atransition in any of the sensors has been read, switched to the highervalue and is maintained on this value until a pre-determined short timeinterval has lapsed without a further detection of a transition on thesensor readings. Apparently, this control scheme may result in togglingbetween the lower and higher value in phases of low angular speed of therotor. FIG. 20C, in contrast, shows a “LED Strobe” that switches to thehigher density value after the angular velocity value derived from thesensor readings exceeds a predetermined threshold value. This schemewould be completed by switching back to the lower value when the samethreshold value or an even lower one is undershot by the calculatedspeed.

The appropriate selection of the specific values for the lower densityand the higher density of the “LED Strobe” may find a starting point inthe following considerations. Assuming the rotor to be in a stationarystate, the first value has to be chosen to provide for sufficientdensity in order to capture the first transition in the “continuousintensity pattern” at either sensor and to allow switching of the strobedensity to the higher value before the next transition passes in frontof either sensor. Here, the critical value can be seen in the maximum inacceleration of the mechanism. Accommodation for higher accelerationrequires more density in strobes at the stationary state and thereforeneeds an increase in the first, lower value. The critical condition forthe second, higher value can be seen in the maximum speed. As explainedbefore, the strobe density must be sufficiently not to produce any kindof artefacts. This very simple digital upwards/downwards switching mayalready provide significant increase in power efficiency for certain usecases wherein, after activation of the sensor operation, the delay intime before the mechanism transitions from a stationary state into anon-stationary state is not predictable and/or the time while themechanism remains in the stationary state is significantly longer thanthe time while the mechanism is in the non-stationary state.Unpredictability, for example, may result from user behaviour. If, as amore specific example, the overall operation of the sensors is triggeredin the way of a wake-up upon detection of a dose setting event or a capremoval event the delay in time until a subsequent expelling operationis started may depend on the time the respective user needs to place theneedle and to start the expelling operation.

Other approaches for determining the increase or decrease in strobedensity over time in order to accommodate for a change in the rotationalstate and/or velocity of the mechanism can be figured out on differentlevels of elaboration.

Additionally, in a situation with a staggered sampling mode wherein thestrobing on the respective sensor has a shift in phase as, for example,explained with reference to FIG. 18B, an adaption of the shift in phasebetween the two sensors may be included. Insofar, the target might beseen in maintaining the phase shift in the “AND” reading as mentionedabove between the angularly offset sensors on a constant value, e.g.90°, independent of the momentary angular speed. The 90° situation wouldresult in an overall detector behaviour identical to the one withexactly 90° offset sensors and synchronous sampling but apart of theneed for powering all light sources at the same time.

Further variants to the outlined embodiment may include approaches forlimiting the need of powering the LED strobing to only one of the two ormore sensor. Apparently, at any point in the timeline of FIGS. 20A, Band C, from the two available sensor readings it can be determinedwhether the next transition will appear at either “Sensor I” or “SensorII” because of the fixed spatial relationship of the sensors. Inparticular, for all points on the timeline with identical sensorreadings, namely “dark”/“dark” and “bright”/“bright”, the subsequenttransition will appear in the timeline of “Sensor II”. The same iscorrect for all points in time where “dark” would be read on thetimeline of “Sensor I” while “bright” would be read on the timeline of“Sensor II”. Only for time points where “bright” would be read from“Sensor I” whereas “dark” would be read from “Sensor II” the nexttransition can be predicted to appear in the timeline of “Sensor I”. Byapplying this scheme, the power consumption for the strobe of thesensors could be further reduced at least in the stationary state of themechanism.

An encoder system according to further embodiments will now be describedwith reference to FIGS. 21 to 29 . This encoder system may be used torecord doses that are delivered from the injection device. The conceptof this encoder system is based on a light guidance used to convey thestatus of an indicator flag to a reflective sensor, which is locatedphysically remote to the flag. The embodiments shown in FIGS. 20 to 28are illustrated with an optical add-on module for an injection device,where the indicator flag is formed by a relative rotation of a number orthe dial sleeve and the injection button, the latter of which houses anoptical sensor. Such an add-on module may be configured to be added to asuitably configured pen injection device for the purpose of recordingdoses that are dialed and delivered from the device. This functionalitymay be of value to a wide variety of device users as a memory aid or tosupport detailed logging of dose history. The module may be configuredto be connectable to a mobile device such as a smartphone or a tabletPC, or similar, to enable the dose history to be downloaded from themodule on a periodic basis. However, the concept of the encoder systemis also applicable to any device with the indicator flag and sensorseparation, for example the injection device 1 of FIG. 1 , wherein themodule may be implemented in the dosage knob 12.

According to the encoder system concept, a collimating optics isarranged between the active face of at least one optical sensor, whichmay be a IR reflective sensor, and a movable dosage programmingcomponent. The collimating optics may comprise one or more discretecollimating lenses and one or more light pipes. The lens geometry may beselected to parallelize (“collimate”) divergent radiation emitted by theat least one optical sensor prior to transmission through the light pipebetween the at least one sensor and the target, namely the indicatorflag.

FIG. 21 shows essential parts of an embodiment of a module 1000implementing this encoder concept: an indicator flag 1008 may be formedby relative rotation of a number sleeve 1006 around a rotation axis1010, wherein the indicator flag 1008 is implemented in the shownembodiment by radially projecting teeth, formed in the top of forexample the number sleeve or the dial sleeve 70 of the injection device1; an optical sensor 215 c and collimating optics comprising twocollimating lenses 1004 a, 1004 b and a light guidance in the form of alight pipe 1002 for conveying the status of the indicator flag 1008 tothe sensor 215 c which is located remote from the flag. The collimatingoptics 1002, 1004 a, 1004 b and the optical sensor 215 c may bepositioned relative to surrounding components within the injectiondevice and particularly associated to an add-on module. As can be seen,the collimating optics comprising the lenses 1004 a, 1004 and the lightpipe 1002 are arranged between the active side, i.e. the IR emitting andreceiving side of the optical sensor 215 c and the indicator flag 1008formed by the number sleeve 1006.

FIG. 22 shows a chassis 1012 housing two optical sensors 215 c(represented by their locations in the chassis 1012 shown by therectangles with bold lines) and their respective collimating lenses 1004a, 1004 b according to an embodiment of a module 1000. The collimatinglenses 1004 a, 1004 b, here implemented by discrete lenses, areenvisaged to be held relative to the optical sensors 2015 c and proximalface of the light pipes by means of a cradle or other locating geometryexisting as a feature within the chassis 1012.

FIG. 23 shows the light pipe 1002 and the guidance of radiation(represented by the dotted arrows) within the light pipe 1002. Thesensor 215 c is arranged in front of the distal end of the light pipe1002, and the target surface, i.e. the indicator flag 1008, in front ofthe pipe's proximal end. The diameter of the light pipe reduces from thedistal to the proximal end so that the light pipe 1002 has the shape ofa frustum. Particularly, the light pipe 1002 may have a circular or anelliptic cross section. The light pipe 1002 helps to better guideradiation emitted by the sensor 215 c to the remote target face orindicator flag 1008, respectively, and radiation reflected from theindicator flag 1008 back to the receiving part of the sensor 215 c.Thus, the signal received by the sensor viewing a reflective surface(the number sleeve) via the light pipe may be improved, which results ina better signal quality due to the improvement in response of theoptical sensor as a result of a greater incident flux on the receiver ofthe optical sensor, which is particularly during normal operation as itmay increase the voltage output of the optical sensor and a highervoltage output may be more easily detectable.

FIG. 24 shows in picture (b) the effect of discrete collimating lenses1004 a and 1004 b arranged between the distal end of the light pipe 1002and the sensor 215 c. Divergent radiation emitted by an active part ofthe sensor 215 c is collimated with the collimating lens 1004 a beforetransmission through the light pipe 1002 to the indicator flag 1008representing the target surface. The radiation reflected by theindicator flag 1008 back into the light pipe 1002 is guided to thecollimator lens 1004 b which collimates the received radiation before itis received by the receiving part of the sensor 215 c. The collimatinglens 1004 a particularly serves to collimate the radiation of adivergent light source such as in LED (Light Emitting Diode) of thesensor 215 c, as shown in the left picture (a) of FIG. 24 . It isenvisaged that the collimating lenses 1004 a, 1004 b may be made of anoptically transparent material, such as glass or polycarbonate,particularly with a good infrared transmissivity in the wavelength rangeof the optical sensor 215 c. To minimize any impact to an increasedlength of the module comprising the collimating optics and the sensor,it is anticipated that the collimating lenses of the collimating opticsshould take the form of lenses featuring aspheric, ornon-constant-curvature surfaces, which permit a collimating effect to beachieved in a smaller form factor optic, as exemplarily shown by thelens in picture (a) of FIG. 24 . Particularly, the detection of a binarystate of a number sleeve target during a “mode shift”, i.e. when thedose or injection button of an injection device is being depressed fromits relaxed state into its 0U position, can be improved with thecollimating lenses. In this case, differentiation between a binary ‘0’and ‘1’ as detected by the optical sensor can be readily obtained for alarge, for example ˜0.5 millimeters, separation between the distal endsof the light pipes and the number sleeve, with components undergoingrelative rotation. Incorporation of the collimating lenses may reducethe divergent effect of the aforementioned gap, facilitatingdisambiguation between a ‘0’ and a ‘1’ as reported by the opticalsensor. Another advantage of the use of the collimating lenses is thepossible reduction of “cross-talk” (light leakage) between neighboredsensor where the outputs from such sensors are sharing the sameoptically contiguous light pipe chassis.

All of the above points relate, fundamentally, to more robust encodingmechanical system where an optical (reflective) sensor form the activeelement in an optical encoder. If the motion of the number sleeverelative to the dose button is more efficiently captured, reducedemitter power of an optical sensor and the use of algorithms requiringfewer microcontroller operations can be utilized, reducing energyconsumption and extending battery life. The encoder system describedabove and in the following with reference to FIGS. 20 to 28 is equallyapplicable to inclusion in a disposable or a re-usable injection device,or any device containing an optical encoder arrangement with a similarlight pipe architecture.

The collimating optics may be implemented as individual, discreetcomponents distinct from an injection moulded light pipe chassis. FIG.25 shows a further embodiment of a chassis 1012 comprising a separateinjection moulded component 1014 fixed in the chassis 1012, which isprovided as holder for all elements of the collimating optics, namelythe collimating lenses 1004 a, 1004 b, and the light pipes 1002. Thecomponent 1014 with the attached collimating lenses 1004 a, 1004 b andseparated from the chassis 1012 is shown in FIG. 26 .

Alternatively, the collimating lenses geometry can also be formeddirectly by part of a tool 1016 provided for creating the light pipechasses 1012, as shown with the embodiment of FIG. 27 . In this case,the lower portion of the lens geometry may be limited to hemispheresowing to the tool action, while the proximal surfaces can be formed asfull (a) spheres. FIG. 28 shows the integral injection moulded chassis1012 comprising also light pipes 1002.

The embodiments described above use two discrete collimating lenses 1004a, 1004 b covering, individually, the transmitting and the receivingportions of the optical sensor, particularly, the optical infraredreflective sensor. However, also other embodiments are possible, as willbe described with reference to FIG. 29 in the following: for example,picture (a) shows an embodiment with a PCB (Printed Circuit Board)mounted, micro-moulded lens array 1004 a covering the sensor 215 c;another example is shown in picture (b), where a single collimating lens1004 a is provided, which covers both the transmitting and receivingportions of the optical sensor 215 c; further embodiments with a singlecollimating lens are shown in pictures (c) and (d): the embodiment ofpicture (c) uses a single collimating lens 1004 b covering the receivingportion of the optical sensor 215 c, and the embodiment of picture (d)uses a single collimating lens 1004 a placed at the distal end of thelight pipe 1002.

Next, embodiments of algorithms for processing the signals, particularlysignal voltages, generated by the optical sensors of sensor arrangementsas described above with regard to the injection device and the moduleare described. The algorithms are implemented as computer programs forexecution by one or more processors, for example of the processorarrangement 23 comprised by the controller 700 as shown in FIG. 7 .

The algorithms are implemented for processing the signals delivered bythe one or more optical sensors 215 a, 215 b, 215 c, namely for decodingthe selected for delivery by or delivered by an injection device. Thealgorithms are particularly applicable to the module described abovewith reference to FIGS. 20 to 28 but is also applicable to the injectiondevice described above with reference to FIGS. 1 to 19B. The algorithmsare preferably applicable to devices with an indicator flag and sensorseparation with light pipes such as the module as described above. Therelative rotation between the dose button and the number sleeve may beencoded optically using an incremental encoder, for example a quadratureencoder, with two or more optical sensors, particularly reflective IRsensors, looking axially at castellations or radially projecting teeth,formed on the top surface of the number sleeve. The encoder system maybe implemented as an add-on module as described above with reference toFIGS. 20 to 28 , which means that the position of the castellations orteeth being detected may vary relative to the positions of the opticalsensors from device to device. Additionally, while the dose button isbeing depressed and released, the axial position of the optical sensorsmay also vary relative to the castellations.

The algorithms described in the following may be implemented in aninjection device or an add-on module particularly for the purpose ofrecording doses that are delivered from the injection device. Thisfunctionality may be of value to a wide variety of injection deviceusers as a memory aid or to support detailed logging of dose history. Itis envisaged that the electronics implementing the algorithms may beconfigured to be connectable to a mobile device such as a smartphone, orsimilar, to enable the dose history to be downloaded from theelectronics on a periodic basis.

The algorithms are configured for detecting the relative rotation ofcastellations or teeth on a number sleeve relative to a non-rotatingcomponent such as the dose button. The presence or otherwise of acastellation or tooth feature provides a binary code, which may be usedto count the number of units dispensed from the injection device. Thevoltage output of the optical sensors may be typically approximated to asinusoid. The algorithms are able to detect the presence or otherwise ofa castellation or tooth feature across all devices, which may have anycombination of geometrical tolerances on the physical features.

Additionally, as the dose button moves axially towards or away from thecastellation or tooth features at the beginning and end of doseejection, the change in the signal generated by the optical sensorshould not be incorrectly interpreted as a rotation of the castellationor tooth features. Therefore, the algorithms may accommodate significantamplitude modulation of the signal generated by the optical sensor.

FIG. 30 shows the typical course of the signal voltages generated by twooptical sensors, which may have a different gain profile to each other.The signal voltages are amplitude modulated. The different gain profilesmay lead to significantly different signal voltages being generated bythe two optical sensors and sent to a processor for processing thesignal voltages. The different gain profiles may be for example due totolerances associated with electronic components.

All of the algorithms pertain to a system with two optical sensors beingarranged with a 180° phase shift so that the signal voltages generatedby both sensors are anti-phase.

A first embodiment of an algorithm applies static thresholding: thealgorithm sets a high threshold and a low threshold for the signalvoltage of the first sensor and for the signal voltage of the secondsensor, respectively; a unit of a dose selected with a movable dosageprogramming component is then counted if the signal voltage of thesecond sensor passes the high threshold and thereafter passes the lowthreshold, followed by the signal voltage of the first sensor passingthe low threshold and thereafter passing the high threshold. Duringmanufacture, a set of calibration geometry may be passed beneath eachsensor at controlled distances to define the high and low thresholds.The thresholds are set for life such that the high threshold is alwaysbelow the largest signal voltage observed during calibration (typicallyat minimum distance of substrate to sensor) and the low threshold isalways below the smallest signal voltage observed during calibration(typically at maximum distance of substrate to sensor). The setthresholds for signal voltage of the first sensor and of the secondsensor are shown in FIG. 31 , which represents the course of the signalvoltages of the first and second sensor. The unit counting isrepresented by the arrows.

A second embodiment of an algorithm applies dynamic thresholding: alsothis algorithm sets a high threshold and a low threshold for the signalvoltage of the first sensor and for the signal voltage of the secondsensor, respectively; a unit of a dose selected with a movable dosageprogramming component is then counted if the signal voltage of thesecond sensor passes the high threshold and thereafter passes the lowthreshold, followed by the signal voltage of the first sensor passingthe low threshold and thereafter passing the high threshold. Thethresholds may with this algorithm determined during the first few unitsdelivered from each dose. As a dose is delivered, a sampling frequencyfor sampling the signal voltages of both sensors is set to a levelhigher than a sampling frequency used for normal operation and thesignal voltages are sampled with the higher sampling frequency duringdelivery of a dose. Then, the magnitudes of at least two consecutivepeak-throughs of the signal voltages of each sensor are determined witha peak-detection algorithm. If the determined magnitudes of at least twoconsecutive peak-throughs are within a predetermined tolerance signalrange, for example a factory-set voltage tolerance, the high thresholdand the low threshold for each signal voltage are then defined basedupon a percentage of the measured peak and through signal voltage valuesor the determined magnitudes of at least two consecutive peak-throughs.This dynamic thresholding is undertaken for both sensors. Once thethresholds have been set, the sampling rate or frequency is reduced to alower level typically used for normal operation, as peak detection is nolonger required. This reduces power consumption of the algorithm. FIG.32 demonstrates the dynamic thresholding by means of the course of thesignal voltages of the first and second sensor.

A third embodiment of an algorithm does not rely on the setting ofthresholds to detect low-high transitions, but rather counts a unit atthe point when the voltage from the second sensor becomes greater thanthe voltage from the first sensor by a defined amount, i.e. thecrossover point between the two sensor voltage signals. A unit iscounted after the signals of the two optical sensors cross over in onedirection, and subsequent units cannot be counted until the signals havecrossed over at least once in the opposite direction. This effectivelycreates a flip-flop latch system. The signals may not deem to have“crossed over” until the difference between the signals, particularlythe voltage difference between them exceeds a threshold value, which maybe set during manufacture. For application of this algorithm, thesignals from the two sensors should be matched in terms of mean voltageand mean amplitude. Since the signals from the two sensors are typicallynot matched in terms of mean voltage and voltage amplitude, as shown bythe course of the two sensor signals in FIG. 33 , they should be matchedby scaling. As such, during manufacture, a set of calibration geometryis passed beneath each sensor at controlled distance and scaling factorsfor mean and amplitude are applied to the second sensor to match themean and amplitude of its signal to the mean and amplitude of the signalof the first sensor. Once, the signals are scaled, the flip-flop dosecounting algorithm can be used to count doses, as illustrated in FIG. 34.

A fourth embodiment of an algorithm is essentially identical to thethird embodiment except that the scaling factors defined to give acommon mean and amplitude for the two sensor signals may be calculatedafter each dose, removing the requirement to “factory set” theseparameters during manufacture. In order to achieve this, the wholedataset for the signals of both sensors is stored, for example bufferedin a memory, and the scaling factors are retrospectively calculated fromthe stored dataset in order to obtain a common mean and amplitudebetween the signals of both sensors. Once the scaling factors have beenapplied, this algorithm is deployed as before such that a unit iscounted after the signals cross over in one direction, and subsequentunits cannot be counted until the signals have crossed over at leastonce in the opposite direction.

A fifth embodiment of an algorithm does not rely on the setting ofthresholds to detect low-high transitions, or the scaling of signals tomatch mean and amplitude, but rather uses a low power peak-detectmethod. A high sampling rate is not required, as the exact voltage valueof the peak is not required, just the detection that a peak hasoccurred, i.e. a point of inflection on the voltage signal of a sensor.A flip-flop latch system may be employed as in other algorithmsdescribed herein in that a unit is counted when a peak is registered onthe signal from the first sensor of two sensors, but subsequent unitscannot be counted until at least one peak has been observed on thesignal of the second sensor. This is illustrated in FIG. 35 . Thisalgorithm does not require scaling or factory setting of thresholds,which makes it robust to coping with tolerance variations and amplitudevariations in use. It is also expected to be low power due to lowcomputational complexity and the potential for a low power sampling ratethan alternative algorithms.

The above described algorithms may permit low sampling frequencies andminimum computational complexity, while accommodating device-to-devicetolerance variations, and in-use signal amplitude variations driven by avariable axial position of the sensor relative to a rotating numbersleeve, particularly teeth or castellations of the sleeve.

A yet further embodiment of an injection device comprising a rotaryencoder system 1100 having a predefined angular periodicity and anencoder ring or wheel 1102 is shown in FIG. 36 . This embodiment can beused as counter for rotations, particularly for dose selection with aninjection pen. The encoder ring 1102 may be arranged within an injectionbutton 1104 of an injection device.

The encoder ring 1102 comprises a plurality of light reflectors arrangedcircumferentially around the encoder ring 1102 with a predefinedperiodicity. The light reflectors are arranged on the axial face side ofthe encoder ring so that light directed towards the light reflectors inan axial direction of the rotary encoder system 1100 may be received andreflected. Each light reflector comprises two reflecting surfaces 1106arranged perpendicular to each other. Thus, incident light 1108 may bereflected from one reflecting surface to the other reflecting surfaceand from the other reflecting surface back to the source of the incidentlight by means of a total internal reflection (TIR) as shown in theright picture of FIG. 36 .

At least the part of the encoder ring 1102 may be made of a transparentmaterial, and the reflecting surfaces 1106 may be high-polished in orderto reflect an amount of incident light back, which may generate a signalamplitude suitable for further processing.

A LED 1112 may be used as light source and two photodiodes 1114 fordetecting the reflected light. The LED 1112 and the photodiodes 1114 maybe arranged on a PCB 1116 of an electronic module for the injectiondevice, which may also comprise electronic for controlling the lightemission by the LED 1112 and process the output signals of thephotodiodes 1114 in order to detect a rotation of either the PCB 1116 orthe encoder ring 1102.

A housing 1118 may be provided for the PCB 1116, for example when theelectronics is comprised by an add-on device for an injection pen. Inorder to allow a passing of light through the housing 1118 it maycomprise an integrated lens 1120 for passing through the light emittedby the LED 1112 and lenses 1122 arranged before the photodiodes 1114 forletting reflected light pass through to the photodiodes 1114. The lens1120 may be adapted to focus the light beams emitted by the LED 1112 onthe reflecting surfaces 1106 of the light reflectors, and the lenses1122 may be adapted to focus the light reflected back from the surfaces1106 on light sensitive areas of the photodiodes 1114.

The button 1104 may comprise a window 1124 being made from a lighttransparent material and apertures 1126 for light emitted by the LED1112 and reflected back from the surface 1106 to the photodiodes 1114.The light emitting and returning path is split by the TIR of thereflecting surfaces 1106 on the apertures 1126, which are placed side byside.

Simulations of the above described encoder concept have shown a goodoptical system performance with a relatively high peak irradiance, asshown in FIG. 37 , which represents the power of two typical outputsignals of the photodiodes 1114. Also, the simulations have shown arelatively high signal-to-noise ratio, and, thus, showing a robustbehaviour.

While the embodiments above have been described in relation tocollecting data from an insulin injector pen, it is noted thatembodiments of the disclosure may be used for other purposes, such asmonitoring of injections of other medicaments.

The terms “drug” or “medicament” are used synonymously herein anddescribe a pharmaceutical formulation containing one or more activepharmaceutical ingredients or pharmaceutically acceptable salts orsolvates thereof, and optionally a pharmaceutically acceptable carrier.An active pharmaceutical ingredient (“API”), in the broadest terms, is achemical structure that has a biological effect on humans or animals. Inpharmacology, a drug or medicament is used in the treatment, cure,prevention, or diagnosis of disease or used to otherwise enhancephysical or mental well-being. A drug or medicament may be used for alimited duration, or on a regular basis for chronic disorders.

As described below, a drug or medicament can include at least one API,or combinations thereof, in various types of formulations, for thetreatment of one or more diseases. Examples of API may include smallmolecules having a molecular weight of 500 Da or less; polypeptides,peptides and proteins (e.g., hormones, growth factors, antibodies,antibody fragments, and enzymes); carbohydrates and polysaccharides; andnucleic acids, double or single stranded DNA (including naked and cDNA),RNA, antisense nucleic acids such as antisense DNA and RNA, smallinterfering RNA (siRNA), ribozymes, genes, and oligonucleotides. Nucleicacids may be incorporated into molecular delivery systems such asvectors, plasmids, or liposomes. Mixtures of one or more drugs are alsocontemplated.

The drug or medicament may be contained in a primary package or “drugcontainer” adapted for use with a drug delivery device. The drugcontainer may be, e.g., a cartridge, syringe, reservoir, or other solidor flexible vessel configured to provide a suitable chamber for storage(e.g., short- or long-term storage) of one or more drugs. For example,in some instances, the chamber may be designed to store a drug for atleast one day (e.g., 1 to at least 30 days). In some instances, thechamber may be designed to store a drug for about 1 month to about 2years. Storage may occur at room temperature (e.g., about 20° C.), orrefrigerated temperatures (e.g., from about −4° C. to about 4° C.). Insome instances, the drug container may be or may include a dual-chambercartridge configured to store two or more components of thepharmaceutical formulation to-be-administered (e.g., an API and adiluent, or two different drugs) separately, one in each chamber. Insuch instances, the two chambers of the dual-chamber cartridge may beconfigured to allow mixing between the two or more components prior toand/or during dispensing into the human or animal body. For example, thetwo chambers may be configured such that they are in fluid communicationwith each other (e.g., by way of a conduit between the two chambers) andallow mixing of the two components when desired by a user prior todispensing. Alternatively or in addition, the two chambers may beconfigured to allow mixing as the components are being dispensed intothe human or animal body.

The drugs or medicaments contained in the drug delivery devices asdescribed herein can be used for the treatment and/or prophylaxis ofmany different types of medical disorders. Examples of disordersinclude, e.g., diabetes mellitus or complications associated withdiabetes mellitus such as diabetic retinopathy, thromboembolismdisorders such as deep vein or pulmonary thromboembolism. Furtherexamples of disorders are acute coronary syndrome (ACS), angina,myocardial infarction, cancer, macular degeneration, inflammation, hayfever, atherosclerosis and/or rheumatoid arthritis. Examples of APIs anddrugs are those as described in handbooks such as Rote Liste 2014, forexample, without limitation, main groups 12 (anti-diabetic drugs) or 86(oncology drugs), and Merck Index, 15th edition.

Examples of APIs for the treatment and/or prophylaxis of type 1 or type2 diabetes mellitus or complications associated with type 1 or type 2diabetes mellitus include an insulin, e.g., human insulin, or a humaninsulin analogue or derivative, a glucagon-like peptide (GLP-1), GLP-1analogues or GLP-1 receptor agonists, or an analogue or derivativethereof, a dipeptidyl peptidase4 (DPP4) inhibitor, or a pharmaceuticallyacceptable salt or solvate thereof, or any mixture thereof. As usedherein, the terms “analogue” and “derivative” refers to a polypeptidewhich has a molecular structure which formally can be derived from thestructure of a naturally occurring peptide, for example that of humaninsulin, by deleting and/or exchanging at least one amino acid residueoccurring in the naturally occurring peptide and/or by adding at leastone amino acid residue. The added and/or exchanged amino acid residuecan either be codable amino acid residues or other naturally occurringresidues or purely synthetic amino acid residues. Insulin analogues arealso referred to as “insulin receptor ligands”. In particular, the term“derivative” refers to a polypeptide which has a molecular structurewhich formally can be derived from the structure of a naturallyoccurring peptide, for example that of human insulin, in which one ormore organic substituent (e.g. a fatty acid) is bound to one or more ofthe amino acids. Optionally, one or more amino acids occurring in thenaturally occurring peptide may have been deleted and/or replaced byother amino acids, including non-codeable amino acids, or amino acids,including non-codeable, have been added to the naturally occurringpeptide.

Examples of insulin analogues are Gly(A21), Arg(B31), Arg(B32) humaninsulin (insulin glargine); Lys(B3), Glu(B29) human insulin (insulinglulisine); Lys(B28), Pro(B29) human insulin (insulin lispro); Asp(B28)human insulin (insulin aspart); human insulin, wherein proline inposition B28 is replaced by Asp, Lys, Leu, Val or Ala and wherein inposition B29 Lys may be replaced by Pro; Ala(B26) human insulin;Des(B28-B30) human insulin; Des(B27) human insulin and Des(B30) humaninsulin.

Examples of insulin derivatives are, for example,B29-N-myristoyl-des(B30) human insulin, Lys(B29)(N-tetradecanoyl)-des(B30) human insulin (insulin detemir, Levemir®);B29-N-palmitoyl-des(B30) human insulin; B29-N-myristoyl human insulin;B29-N-palmitoyl human insulin; B28-N-myristoyl LysB28ProB29 humaninsulin; B28-N-palmitoyl-LysB28ProB29 human insulin;B30-N-myristoyl-ThrB29LysB30 human insulin; B30-N-palmitoyl-ThrB29LysB30human insulin; B29-N-(N-palmitoyl-gamma-glutamyl)-des(B30) humaninsulin, B29-N-omega-carboxypentadecanoyl-gamma-L-glutamyl-des(B30)human insulin (insulin degludec, Tresiba®);B29-N-(Nlithocholyl-gamma-glutamyl)-des(B30) human insulin;B29-N-(ω-carboxyheptadecanoyl)des(B30) human insulin andB29-N-(ω-carboxyheptadecanoyl) human insulin.

Examples of GLP-1, GLP-1 analogues and GLP-1 receptor agonists are, forexample, Lixisenatide (Lyxumia®), Exenatide (Exendin-4, Byetta®,Bydureon®, a 39 amino acid peptide which is produced by the salivaryglands of the Gila monster), Liraglutide (Victoza®), Semaglutide,Taspoglutide, Albiglutide (Syncria®), Dulaglutide (Trulicity®),rExendin-4, CJC-1134-PC, PB-1023, TTP-054, Langlenatide/HM-11260C, CM-3,GLP-1 Eligen, ORMD-0901, NN-9924, NN-9926, NN-9927, Nodexen,Viador-GLP-1, CVX-096, ZYOG-1, ZYD-1, GSK-2374697, DA3091, MAR-701,MAR709, ZP-2929, ZP-3022, TT-401, BHM-034. MOD-6030, CAM-2036, DA15864,ARI-2651, ARI-2255, Exenatide-XTEN and Glucagon-Xten.

An examples of an oligonucleotide is, for example: mipomersen sodium(Kynamro®), a cholesterol-reducing antisense therapeutic for thetreatment of familial hypercholesterolemia. Examples of DPP4 inhibitorsare Vildagliptin, Sitagliptin, Denagliptin, Saxagliptin, Berberine.Examples of hormones include hypophysis hormones or hypothalamushormones or regulatory active peptides and their antagonists, such asGonadotropine (Follitropin, Lutropin, Choriongonadotropin, Menotropin),Somatropine (Somatropin), Desmopressin, Terlipressin, Gonadorelin,Triptorelin, Leuprorelin, Buserelin, Nafarelin, and Goserelin.

Examples of polysaccharides include a glucosaminoglycane, a hyaluronicacid, a heparin, a low molecular weight heparin or an ultra-lowmolecular weight heparin or a derivative thereof, or a sulphatedpolysaccharide, e.g. a poly-sulphated form of the above-mentionedpolysaccharides, and/or a pharmaceutically acceptable salt thereof. Anexample of a pharmaceutically acceptable salt of a poly-sulphated lowmolecular weight heparin is enoxaparin sodium. An example of ahyaluronic acid derivative is Hylan G-F 20 (Synvisc®), a sodiumhyaluronate.

The term “antibody”, as used herein, refers to an immunoglobulinmolecule or an antigen-binding portion thereof. Examples ofantigen-binding portions of immunoglobulin molecules include F(ab) andF(ab′)2 fragments, which retain the ability to bind antigen. Theantibody can be polyclonal, monoclonal, recombinant, chimeric,de-immunized or humanized, fully human, non-human, (e.g., murine), orsingle chain antibody. In some embodiments, the antibody has effectorfunction and can fix complement. In some embodiments, the antibody hasreduced or no ability to bind an Fc receptor. For example, the antibodycan be an isotype or subtype, an antibody fragment or mutant, which doesnot support binding to an Fc receptor, e.g., it has a mutagenized ordeleted Fc receptor binding region. The term antibody also includes anantigen-binding molecule based on tetravalent bispecific tandemimmunoglobulins (TBTI) and/or a dual variable region antibody-likebinding protein having cross-over binding region orientation (CODV).

The terms “fragment” or “antibody fragment” refer to a polypeptidederived from an antibody polypeptide molecule (e.g., an antibody heavyand/or light chain polypeptide) that does not comprise a full-lengthantibody polypeptide, but that still comprises at least a portion of afull-length antibody polypeptide that is capable of binding to anantigen. Antibody fragments can comprise a cleaved portion of a fulllength antibody polypeptide, although the term is not limited to suchcleaved fragments. Antibody fragments that are useful in the presentdisclosure include, for example, Fab fragments, F(ab′)2 fragments, scFv(single-chain Fv) fragments, linear antibodies, monospecific ormultispecific antibody fragments such as bispecific, trispecific,tetraspecific and multispecific antibodies (e.g., diabodies, triabodies,tetrabodies), monovalent or multivalent antibody fragments such asbivalent, trivalent, tetravalent and multivalent antibodies, minibodies,chelating recombinant antibodies, tribodies or bibodies, intrabodies,nanobodies, small modular immunopharmaceuticals (SMIP), binding-domainimmunoglobulin fusion proteins, camelized antibodies, and VHH containingantibodies. Additional examples of antigen-binding antibody fragmentsare known in the art.

The terms “Complementarity-determining region” or “CDR” refer to shortpolypeptide sequences within the variable region of both heavy and lightchain polypeptides that are primarily responsible for mediating specificantigen recognition. The term “framework region” refers to amino acidsequences within the variable region of both heavy and light chainpolypeptides that are not CDR sequences, and are primarily responsiblefor maintaining correct positioning of the CDR sequences to permitantigen binding. Although the framework regions themselves typically donot directly participate in antigen binding, as is known in the art,certain residues within the framework regions of certain antibodies candirectly participate in antigen binding or can affect the ability of oneor more amino acids in CDRs to interact with antigen. Examples ofantibodies are anti PCSK-9 mAb (e.g., Alirocumab), anti IL-6 mAb (e.g.,Sarilumab), and anti IL-4 mAb (e.g., Dupilumab).

Pharmaceutically acceptable salts of any API described herein are alsocontemplated for use in a drug or medicament in a drug delivery device.Pharmaceutically acceptable salts are for example acid addition saltsand basic salts.

Those of skill in the art will understand that modifications (additionsand/or removals) of various components of the APIs, formulations,apparatuses, methods, systems and embodiments described herein may bemade without departing from the full scope and spirit of the presentdisclosure, which encompass such modifications and any and allequivalents thereof.

The invention claimed is:
 1. An injection device comprising: a movabledosage programming component comprising a rotary encoder system having apredefined angular periodicity; a sensor arrangement comprising a firstsensor and a second sensor configured to detect movement of the rotaryencoder system relative to the sensor arrangement during dispensing of amedicament, wherein the first sensor and the second sensor areconfigured to operate in a strobe-sampling mode in which each of thesensors is switched on and off intermittently at a controlled frequency;and a processor arrangement configured to, based on the movement,determine a medicament dosage administered by the injection device. 2.The injection device of claim 1, wherein the rotary encoder systemcomprises an encoder ring comprising a plurality of substantially lightreflective segments arranged circumferentially around the encoder ringin accordance with a predefined periodicity.
 3. The injection device ofclaim 2, wherein the encoder ring comprises a plurality of substantiallylight absorbent segments arranged to alternate with the plurality ofsubstantially light reflective segments in accordance with thepredefined periodicity.
 4. The injection device of claim 1, wherein theencoder system comprises twelve alternating regions.
 5. The injectiondevice of claim 1, wherein the first sensor and the second sensor havean angular offset substantially equal to half of the predefined angularperiodicity.
 6. The injection device of claim 1, wherein the firstsensor and the second sensor are configured to operate in a synchronousmode of operation.
 7. The injection device of claim 1, wherein the firstsensor and the second sensor are mounted in an injection button of theinjection device.
 8. The injection device of claim 7, wherein the firstsensor and the second sensor are configured to sense a relativerotational position or to sense a rotational position change of a dialsleeve relative to the injection button.
 9. The injection device ofclaim 8, wherein the first sensor and the second sensor are configuredto target adapted regions of the dial sleeve which are divided intoreflective and absorbent segments.
 10. The injection device of claim 1,wherein signals of the first sensor and the second sensor are configuredto be transformed into a 2-bit Gray code output.
 11. The injectiondevice of claim 1, wherein the first sensor and the second sensor arearranged to be out of phase with each other such that an angle betweenthem equates an odd number of units.
 12. The injection device of claim1, wherein the first sensor and the second sensor are configured tooperate in the strobe-sampling mode at a frequency that increases withan increase in angular velocity of the first sensor and second sensor.13. The injection device of claim 12, wherein the frequency is variedbased on a relative rotational speed of the rotary encoder system withrespect to the first sensor and the second sensor.
 14. The injectiondevice of claim 1, further comprising an injection button and anelectrical switch connected to the sensor arrangement, the electricalswitch arranged to supply power to the sensor arrangement in response toactuation of the injection button.
 15. The injection device of claim 1,wherein each of the first sensor and the second sensor comprises anoptical sensor configured to detect light reflected by the encodersystem.
 16. The injection device of claim 1, further comprising amedicament containing cartridge.
 17. The injection device of claim 1,comprising a dosage knob configured to be turned for programming a doseof medicament to be ejected from the injection device.
 18. The injectiondevice of claim 17, comprising a dial sleeve that is configured to movein response to turning of the dosage knob.
 19. The injection device ofclaim 17, wherein the dosage knob is an injection button configured tobe pushed in an axial direction to eject the dose of the medicament. 20.The injection device of claim 18, wherein the movable dosage programmingcomponent comprises the dial sleeve, and the dial sleeve is rotatable toreturn to an initial position during delivery of the dose of themedicament.
 21. The injection device of claim 1, wherein the processorarrangement includes one or more processors.
 22. The injection device ofclaim 1, comprising a wireless communication interface.
 23. Theinjection device of claim 1, comprising a battery.
 24. The injectiondevice of claim 1, wherein the sensor arrangement comprises LEDsconfigured to vary a strobe of the LEDs in the strobe-sampling mode.